JPH0587768A - Biosensor - Google Patents
BiosensorInfo
- Publication number
- JPH0587768A JPH0587768A JP3143803A JP14380391A JPH0587768A JP H0587768 A JPH0587768 A JP H0587768A JP 3143803 A JP3143803 A JP 3143803A JP 14380391 A JP14380391 A JP 14380391A JP H0587768 A JPH0587768 A JP H0587768A
- Authority
- JP
- Japan
- Prior art keywords
- glucose
- inhibitor
- biosensor
- electrode
- substrate
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
Landscapes
- Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
Abstract
Description
【0001】[0001]
【産業上の利用分野】本発明は膜電位または電極反応で
得られる電流値を測定する電極型のバイオセンサに関す
る。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an electrode type biosensor for measuring a membrane potential or a current value obtained by an electrode reaction.
【0002】[0002]
【従来の技術】血液中のグルコース濃度を簡単に測定し
得る電極型のバイオセンサとして、特開昭60−211
350号に開示されるものが知られている。このバイオ
センサは測定極にグルコースを酸化するグルコースオキ
シダーゼとこれと共役する酸化型色素を担持する多孔体
を設けた構造になっている。2. Description of the Related Art As an electrode type biosensor which can easily measure the glucose concentration in blood, Japanese Patent Application Laid-Open No. 60-221
The one disclosed in No. 350 is known. This biosensor has a structure in which a measuring electrode is provided with a glucose oxidase which oxidizes glucose and a porous body which carries an oxidative dye conjugated thereto.
【0003】その作用は、生体試料液(血液)を多孔体
に接触させ、グルコースオキシダーゼによってグルコー
スを酸化せしめ、これと同時に酸化型色素を還元し、こ
の還元された色素を電極で酸化するのに要した酸化電流
値からグルコース濃度を知るようにしたものである。そ
して、上記の酸化電流値にはアスコルビン酸等の阻害物
質を酸化した電流値も含まれているため、対極において
阻害物質を酸化し、この電流値を測定極における酸化電
流値から引くことで、グルコースの真の濃度を算出する
ようにしている。The action is to bring a biological sample solution (blood) into contact with a porous body, oxidize glucose by glucose oxidase, simultaneously reduce an oxidized dye, and oxidize the reduced dye at an electrode. The glucose concentration is known from the required oxidation current value. And, since the oxidation current value includes the current value obtained by oxidizing the inhibitor such as ascorbic acid, the inhibitor is oxidized at the counter electrode, and the current value is subtracted from the oxidation current value at the measurement electrode. The true concentration of glucose is calculated.
【0004】[0004]
【発明が解決しようとする課題】上述した従来のバイオ
センサにあっては、測定極において阻害物質の酸化のた
めに要した電流値と、対極において阻害物質の酸化のた
めに要した電流値とが等しいという前提にたっている
が、測定極における阻害物質濃度と対極における阻害物
質濃度は常に同一ではなく、また酵素拡散抵抗の差など
により正確な濃度を測定することができない。In the above-mentioned conventional biosensor, the current value required for oxidation of the inhibitor at the measurement electrode and the current value required for oxidation of the inhibitor at the counter electrode However, the inhibitor concentration at the measurement electrode and the inhibitor concentration at the counter electrode are not always the same, and an accurate concentration cannot be measured due to the difference in enzyme diffusion resistance.
【0005】[0005]
【課題を解決するための手段】上記課題を解決すべく本
発明は、電極型バイオセンサに、グルコースなどの基質
を酸化せしめる酸化還元酵素(グルコースオキシダー
ゼ)及び酸化型色素の他にアスコルビン酸などの阻害物
質を酸化する酵素(アスコルビン酸オキシダーゼ)を担
持する固定化酵素膜を設けた。Means for Solving the Problems To solve the above problems, the present invention provides an electrode-type biosensor which includes a redox enzyme (glucose oxidase) that oxidizes a substrate such as glucose and an oxidative dye, and ascorbic acid. An immobilized enzyme membrane carrying an enzyme (ascorbate oxidase) that oxidizes the inhibitor was provided.
【0006】[0006]
【作用】アスコルビン酸オキシダーゼなどの阻害物質を
酸化する酵素を担持した固定化酵素膜を設けることで、
電極での阻害物質の酸化がなくなる。[Function] By providing an immobilized enzyme membrane carrying an enzyme that oxidizes an inhibitor such as ascorbate oxidase,
Oxidation of the inhibitor at the electrode is eliminated.
【0007】[0007]
【実施例】以下に本発明の実施例を添付図面に基づいて
説明する。ここで、図1は本発明に係るバイオセンサの
要部断面図である。Embodiments of the present invention will be described below with reference to the accompanying drawings. Here, FIG. 1 is a cross-sectional view of a main part of the biosensor according to the present invention.
【0008】バイオセンサは筒状ケース1の先端部を生
体試料液が接する緻密層2とし、この緻密層2の下に順
次非対称の多孔質層3、固定化酵素膜4、酸素透過膜5
及び白金からなるカソード電極6を設け、またケース1
内はKOH等の電解質溶液を満たし、更に鉛などからな
るアノード電極7を設けている。In the biosensor, the distal end of the cylindrical case 1 is a dense layer 2 in contact with a biological sample solution, and under the dense layer 2, an asymmetric porous layer 3, an immobilized enzyme membrane 4, and an oxygen permeable membrane 5 are successively arranged.
And a cathode electrode 6 made of platinum, and the case 1
The inside is filled with an electrolyte solution such as KOH, and further, an anode electrode 7 made of lead or the like is provided.
【0009】ここで非対称の多孔質層3は酢酸セルロー
スからなり、その厚みは60μm程度とし、また緻密層
2側を密に固定化酵素膜4側を粗にし、グルコースより
も大きな分子の侵入を阻止するとともに、一旦取り込ん
だグルコース分子はすばやく固定化酵素膜4に到達せし
めるようにしている。Here, the asymmetric porous layer 3 is made of cellulose acetate and has a thickness of about 60 μm. The dense layer 2 side is densely packed and the immobilized enzyme membrane 4 side is roughened so that molecules larger than glucose can enter. In addition to blocking, the glucose molecules once taken in are allowed to reach the immobilized enzyme membrane 4 quickly.
【0010】固定化酵素膜4は厚みが40μm程度のコ
ラーゲン膜からなり、アスコルビン酸を酸化するアスコ
ルビン酸オキシダーゼ8、グルコースを酸化するグルコ
ースオキシダーゼ9及びフェリシアン化カリウム等の酸
化型色素10を担持している。The immobilized enzyme membrane 4 is composed of a collagen membrane having a thickness of about 40 μm, and carries ascorbic acid oxidase 8 which oxidizes ascorbic acid, glucose oxidase 9 which oxidizes glucose and an oxidative dye 10 such as potassium ferricyanide. ..
【0011】ここで、図示例にあってはグルコースオキ
シダーゼ9をカソード電極6に近い層に、アスコルビン
酸オキシダーゼ8をカソード電極6から離れた層に固定
化せしめたが、各酵素を層分けせず膜内にランダムに配
置してもよい。また阻害物質を酸化する酵素としてはア
スコルビン酸オキシダーゼ8の他にウリカーゼを固定化
してもよい。In the illustrated example, glucose oxidase 9 was immobilized in a layer close to the cathode electrode 6 and ascorbate oxidase 8 was immobilized in a layer distant from the cathode electrode 6, but each enzyme was not divided into layers to form a membrane. They may be randomly arranged inside. As the enzyme that oxidizes the inhibitor, uricase may be immobilized in addition to ascorbate oxidase 8.
【0012】以上において、生体試料液をセンサに接触
させると基質であるグルコース及び阻害物質であるアス
コルビン酸が緻密層2、多孔質層3を透過して固定化酵
素膜4に拡散してきて、以下の(化1)に示す反応式に
したがって酸化せしめられる。When the biological sample solution is brought into contact with the sensor as described above, glucose as a substrate and ascorbic acid as an inhibitor permeate through the dense layer 2 and the porous layer 3 and diffuse into the immobilized enzyme membrane 4. Oxidation is performed according to the reaction formula shown in (Chemical formula 1).
【0013】[0013]
【化1】 [Chemical 1]
【0014】そして、上記と同時に酸化型色素であるフ
ェリシアン化カリウムが還元されてフェロシアン化カリ
ウムとなり、この還元されたフェロシアン化カリウムを
カソード電極6で酸化するのに要した酸化電流値からグ
ルコース濃度を知るのであるが、本発明にあっては阻害
物質であるアスコルビン酸は電極に到達するまでに既に
酸化せしめられているので、上記の酸化電流値は色素を
酸化せしめるのに要した電流値で、アスコルビン酸を酸
化するのに要した電流値は含まれないことになる。した
がって、上記の酸化電流値と生体試料液中のグルコース
濃度とは良く一致することとなる。Simultaneously with the above, potassium ferricyanide, which is an oxidation type dye, is reduced to potassium ferrocyanide, and the glucose concentration is known from the oxidation current value required for oxidizing the reduced potassium ferrocyanide at the cathode electrode 6. However, in the present invention, ascorbic acid, which is an inhibitor, has already been oxidized by the time it reaches the electrode.Therefore, the above-mentioned oxidation current value is the current value required to oxidize the dye. The current value required for oxidation is not included. Therefore, the oxidation current value and the glucose concentration in the biological sample solution are in good agreement.
【0015】尚、実施例にあっては、酸素電極を用いて
グルコース濃度を測定する場合について説明したが、過
酸化水素電極を用いてグルコース濃度を測定することも
可能である。この場合にはアスコルビン酸の悪影響は防
ぐことができるのでアスコルビン酸オキシダーゼを固定
化する必要はないが、阻害物質として混在する尿酸は酸
化されると過酸化水素を生成するので、尿酸の酸化酵素
であるウリカーゼを固定化することが必要となる。In the examples, the case where the glucose concentration is measured using the oxygen electrode has been described, but it is also possible to measure the glucose concentration using the hydrogen peroxide electrode. In this case, it is not necessary to immobilize ascorbate oxidase because the adverse effect of ascorbic acid can be prevented, but since uric acid mixed as an inhibitor produces hydrogen peroxide when oxidized, uric acid oxidase is used. It is necessary to immobilize a certain uricase.
【0016】[0016]
【発明の効果】図2はアスコルビン酸濃度と電流値との
関係について本発明と従来例とを比較したグラフであ
り、図3はグルコース濃度と電流値との関係について本
発明と従来例とを比較したグラフである。図2からは本
発明によればアスコルビン酸の濃度が3%程度になるま
で測定値に信頼性があることが分り、図3からはグルコ
ース濃度と酸化電流値とが高濃度まで良く比例すること
が分る。FIG. 2 is a graph comparing the present invention and the conventional example with respect to the relationship between the ascorbic acid concentration and the current value, and FIG. 3 shows the relationship between the present invention and the conventional example with respect to the relationship between the glucose concentration and the current value. It is the graph which compared. From FIG. 2, it can be seen that according to the present invention, the measured value is reliable until the concentration of ascorbic acid reaches about 3%, and from FIG. 3, the glucose concentration and the oxidation current value are well proportional to a high concentration. I understand.
【0017】以上の説明及びグラフから明らかなように
本発明によれば、電極型バイオセンサの測定極及び対極
の双方にアスコルビン酸や尿酸などの阻害物質を酸化す
る酵素を担持した固定化酵素膜を設けたので、これら阻
害物質が電極上で酸化せしめられることがなくなり、結
局測定極での酸化電流はそのまま基質の濃度に比例する
ことになり、正確な濃度を測定することができる。As is apparent from the above description and graphs, according to the present invention, an immobilized enzyme membrane carrying an enzyme that oxidizes an inhibitor such as ascorbic acid or uric acid on both the measurement electrode and the counter electrode of an electrode type biosensor. Since such a substance is provided, these inhibitors are not oxidized on the electrode, and the oxidation current at the measuring electrode is in proportion to the concentration of the substrate as it is, so that the accurate concentration can be measured.
【図1】本発明に係るバイオセンサの要部断面図FIG. 1 is a sectional view of an essential part of a biosensor according to the present invention.
【図2】アスコルビン酸濃度と電流値との関係について
本発明と従来例とを比較したグラフFIG. 2 is a graph comparing the present invention with a conventional example regarding the relationship between the ascorbic acid concentration and the current value.
【図3】グルコース濃度と電流値との関係について本発
明と従来例とを比較したグラフFIG. 3 is a graph comparing the present invention with a conventional example regarding the relationship between glucose concentration and current value.
1…ケース、2…緻密層、3…多孔質層、4…固定化酵
素膜、6…カソード電極、8…阻害物質酸化酵素、9…
基質酸化酵素、10…酸化型色素。1 ... Case, 2 ... Dense layer, 3 ... Porous layer, 4 ... Immobilized enzyme membrane, 6 ... Cathode electrode, 8 ... Inhibitor oxidase, 9 ...
Substrate oxidase, 10 ... Oxidizing dye.
Claims (2)
めた後の酸素濃度または基質の酸化によって生成される
反応物質濃度を検知して試料中の基質濃度を測定するよ
うにしたバイオセンサにおいて、このバイオセンサは膜
電位または電極反応で得られる電流値を測定する電極型
バイオセンサとし、また基質を酸化せしめる酸化還元酵
素及び酸化還元酵素と共役する酸化型色素の他に阻害物
質を酸化する酵素を担持する固定化酵素膜を有すること
を特徴とするバイオセンサ。1. A biosensor in which the substrate concentration in a sample is measured by detecting the oxygen concentration after oxidizing the substrate in the presence of oxidoreductase or the concentration of a reaction substance produced by the oxidation of the substrate. , This biosensor is an electrode-type biosensor that measures the membrane potential or the current value obtained by the electrode reaction, and it also oxidizes the redox enzyme that oxidizes the substrate and the oxidation dye that couples with the redox enzyme, as well as the inhibitor. A biosensor having an immobilized enzyme membrane carrying an enzyme.
還元酵素はグルコースオキシダーゼであり、前記阻害物
質はアスコルビン酸または尿酸であり、更に前記阻害物
質を酸化する酵素はアスコルビン酸オキシダーゼまたは
ウリカーゼであることを特徴とする請求項1に記載のバ
イオセンサ。2. The substrate is glucose, the redox enzyme is glucose oxidase, the inhibitor is ascorbic acid or uric acid, and the enzyme that oxidizes the inhibitor is ascorbate oxidase or uricase. The biosensor according to claim 1, wherein:
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP3143803A JPH0587768A (en) | 1991-05-20 | 1991-05-20 | Biosensor |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP3143803A JPH0587768A (en) | 1991-05-20 | 1991-05-20 | Biosensor |
Publications (1)
Publication Number | Publication Date |
---|---|
JPH0587768A true JPH0587768A (en) | 1993-04-06 |
Family
ID=15347347
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP3143803A Pending JPH0587768A (en) | 1991-05-20 | 1991-05-20 | Biosensor |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPH0587768A (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1482056A2 (en) * | 2003-05-28 | 2004-12-01 | Matsushita Electric Industrial Co., Ltd. | Biosensor |
-
1991
- 1991-05-20 JP JP3143803A patent/JPH0587768A/en active Pending
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1482056A2 (en) * | 2003-05-28 | 2004-12-01 | Matsushita Electric Industrial Co., Ltd. | Biosensor |
EP1482056A3 (en) * | 2003-05-28 | 2006-01-04 | Matsushita Electric Industrial Co., Ltd. | Biosensor |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
JP6150262B2 (en) | Analyte biosensor system | |
JP3413323B2 (en) | Method and apparatus for measuring the concentration of an analyte utilizing an amperometric sensor | |
US8877035B2 (en) | Gated amperometry methods | |
RU2372588C2 (en) | Method and device for realising threshold value-based correction functions for biosensors | |
RU2491549C2 (en) | Amperometry with strobing and fast reading | |
US9938555B2 (en) | Determination of hydrogen peroxide concentrations | |
RU2007141387A (en) | OXIDIZABLE TYPES OF COMPOUNDS AS AN INTERNAL STANDARD IN CONTROL SOLUTIONS FOR BIOSENSORS | |
JPH0617889B2 (en) | Biochemical sensor | |
JP2007523326A (en) | Oxidizable species as internal standards for biosensors and methods of use | |
KR102119301B1 (en) | Method and test element for electrochemically detecting at least one analyte in a sample of a body fluid | |
JPH11344462A (en) | Method for determining substrate | |
JPH0587768A (en) | Biosensor | |
US10285633B2 (en) | Implantable electrochemical biosensor system and method | |
JPH0345336B2 (en) | ||
Christiansen et al. | The slow penetration of enzymebased biosensors into clinical chemistry analysis | |
US20230051071A1 (en) | Analyte sensor and a method for producing an analyte sensor | |
JP4249549B2 (en) | Sample measuring apparatus and sample measuring method | |
KR20210042486A (en) | Electrochemical biosensor and manufacturing method thereof | |
JPS62235557A (en) | Enzyme electrode | |
JPS62240849A (en) | Enzyme electrode | |
JPS63139244A (en) | Glucose sensor | |
JPH1123515A (en) | Quantitative method for matrix | |
JPS6459056A (en) | Biosensor | |
JPH043822B2 (en) | ||
JPS60135754A (en) | Concentration measuring device |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
A02 | Decision of refusal |
Free format text: JAPANESE INTERMEDIATE CODE: A02 Effective date: 19991109 |